Analog heater control for medical instrument

ABSTRACT

An instrument for determining a characteristic of a biological fluid or a control includes a heater and a heater control. The heater comprises a heater element, supported in heat conducting relationship to the biological fluid or control when the instrument is in use. A temperature sensitive element monitors the temperature of the heater element support. The heater control comprises a first temperature setpoint control for controlling the heater to maintain the temperature of the biological fluid or control at about a first temperature and a second temperature setpoint control for overriding the first temperature setpoint control to heat the biological fluid or control toward a second temperature.

This application is a continuation of application Ser. No. 08/114,915, filed Aug. 31, 1993, now abandoned.

This is a related application to U.S. Ser. No. 08/114,914, titled POWER SUPPLY MONITOR AND CONTROL FOR MEDICAL INSTRUMENT, U.S. Ser. No. 08/114,913, titled FLUID DOSE, FLOW AND COAGULATION SENSOR FOR MEDICAL INSTRUMENT, U.S. Ser. No. 08/114,894, titled MAGNETIC SYSTEM FOR MEDICAL INSTRUMENT, U.S. Ser. No. 08/114,579, titled REAGENT AND METHOD OF ITS USE, and U.S. Ser. No. 08/114,897, titled METHOD AND APPARATUS FOR OPERATING A MEDICAL INSTRUMENT, all filed on the same date as this application and assigned to the same assignee, the disclosure of which is incorporated herein by reference.

This invention relates to method and apparatus for eliminating switching noise produced by, and characteristic of, digital control circuitry. It is disclosed in the context of digital control circuitry for a blood coagulation instrument, but is believed to be useful in other contexts as well.

At present, heater plate controls for blood coagulation testing instruments and the like employ algorithm-based, proportional-integral-derivative (PID) controllers. These types of controllers employ microcontrollers (μC's) which use analog-to-digital (A/D) converted heater plate temperature data and a stored PID control algorithm to determine and update continuously a current source duty cycle.

The present invention provides continuous control rather than the prior art PID-A/D controller's discrete control. Continuous control provides infinite resolution as opposed to the prior art's discrete resolutions. PID-A/D controllers are limited in their accuracy by such parameters as A/D converter and μC input/output (I/O) sampling rates. The continuous analog system of the invention therefore imparts less ripple about the setpoint temperature than such prior art systems. This enhanced temperature control is important, particularly in instruments in which a very small sample of, for example, blood is being analyzed for a somewhat temperature-sensitive characteristic, such as coagulation time.

According to the invention, the heat output of a heater plate is programmed and regulated. Illustratively, it is programmed and regulated to control the heat of the heater plate at one of two different predetermined temperatures.

According to an illustrative embodiment of the invention, a thermistor which monitors the temperature of the heater plate is the feedback element of an analog heater control. The thermistor is coupled in a variable resistance leg of a bridge circuit. An operational amplifier is coupled to the bridge circuit and seeks to balance the bridge by varying the power supplied by the operational amplifier's output terminal via a transistor to the heater plate. A μC selects one of the two predetermined temperatures, based upon certain control parameters, and provides this information to the operational amplifier. The μC also enables/disables the heater control circuitry. A fail-safe circuit is employed to prevent thermal runaway of the heater plate in the event of thermistor open circuit failure, removal of the thermistor from circuit, or the like.

The heater control circuit is designed to bring a heater element, such as a blood sample heater plate, to a desired setpoint temperature and regulate the system to that temperature. The system is hardware programmable to two desired setpoint temperatures, illustratively 44° C. to heat a blood sample quickly from room temperature toward body temperature, and 39° C. to maintain the sample at body temperature during the clotting time test. The setpoint temperatures are selected by the μC I/O port line. The μC also controls enabling and disabling of the control circuit.

The feedback element in the temperature control circuit is a thermistor. The thermistor is an element of a variable leg of a bridge circuit. The bridge circuit is coupled to an input terminal of a differential amplifier. The differential amplifier senses the voltage differential between a reference leg of the bridge circuit and the variable leg with the thermistor element. The differential amplifier output terminal drives the heater plate accordingly in order to meet the desired setpoint temperature. Once the system has reached the desired setpoint temperature, the bridge circuit will be balanced and the differential amplifier will continue to keep the bridge balance, regulating the heater plate temperature at the desired set point.

The system is provided with fault protection to prevent a hazardous overheating condition if the thermistor is damaged or is missing from the bridge circuit. The heater control circuit shuts down in response to sensing of a fault. In addition, to minimize overheating of the heater element, the μC is programmed to drive the heater element to a predetermined maximum power limit. The μC can also monitor the drive to the heater element to determine whether the circuitry is functioning properly.

According to an aspect of the invention, a combination heater and heater control is provided for an instrument for monitoring a reaction which occurs when the reactants are heated. The heater comprises an electrically resistive pattern. Means are provided for supporting the pattern in heat conducting relationship to the reactants when the instrument is in use. Means are provided for monitoring the temperature of the support means. The means for monitoring the temperature of the support means is mounted adjacent the support means. The monitoring means and pattern are coupled to the heater control.

Illustratively, the system is incorporated into an instrument for determining the coagulation time of blood, a blood fraction or a control. The instrument comprises a first temperature setpoint control and a second temperature setpoint control.

According to another aspect of the invention, an instrument for determining the coagulation time of blood, a blood fraction or a control includes a heater and a heater control. The heater comprises a heater element. Means are provided for supporting the heater element in heat conducting relationship to the blood, blood fraction or control when the instrument is in use. Means are provided for monitoring the temperature of the support means. The means for monitoring the temperature of the support means is mounted adjacent the support means. The heater control comprises a first temperature setpoint control and a second temperature setpoint control. The monitoring means and the heater element are coupled to the heater control.

Additionally, illustratively, the instrument comprises a controller and the second temperature setpoint control comprises an output terminal of the controller for providing a signal that the support means is to be heated from ambient temperature for conducting a coagulation time test.

Further, illustratively, the heater control, the monitoring means and the means for coupling the monitoring means to the heater control together comprise a differential amplifier and a bridge circuit having first, second, third and fourth bridge legs. The differential amplifier includes an inverting input terminal and a non-inverting input terminal. The inverting input terminal and the first and second legs of the bridge are coupled together in a circuit. The non-inverting input terminal and the third and fourth legs of the bridge are coupled together in a circuit. The second leg of the bridge includes the first temperature setpoint control. The fourth leg of the bridge includes the means for monitoring the temperature of the support means.

Illustratively, the means for monitoring the temperature of the support means comprises a temperature sensitive element.

Additionally, illustratively, the first temperature setpoint control comprises a potentiometer for setting the temperature at which the support means is to be maintained during the reaction.

The invention may best be understood by referring to the following description and accompanying drawings which illustrate the invention. In the drawings:

FIG. 1 illustrates an exploded perspective view of an instrument constructed according to the present invention;

FIG. 2 illustrates a fragmentary exploded perspective view of the bottom portion of the instrument illustrated in FIG. 1;

FIG. 3 illustrates a fragmentary exploded perspective view of the top portion of the instrument illustrated in FIG. 1;

FIG. 4 illustrates an exploded perspective view of a detail of FIG. 1;

FIG. 5 illustrates an exploded perspective views of a detail of FIG. 4;

FIG. 6 illustrates an enlarged exploded perspective view of a detail of FIG. 5;

FIGS. 7a-b illustrate an enlarged, fragmentary, exploded perspective view and a fragmentary bottom plan view, respectively, of a detail of FIG. 5;

FIGS. 8a-c illustrate a top perspective view, a different top perspective view, and a bottom perspective view, respectively, of a detail of FIG. 5;

FIGS. 9a-b illustrate an exploded bottom perspective view and an exploded top perspective view, respectively, of a detail of FIG. 5;

FIG. 10 illustrates a top plan view of a detail of FIG. 5;

FIGS. 11a-d illustrate exploded perspective views of details of FIG. 4;

FIGS. 12a-b illustrate perspective views from two different perspectives of a detail of FIG. 4;

FIG. 13 illustrates a block diagram of the electrical system of the instrument of FIG. 1;

FIG. 14 illustrates a schematic diagram of an electric circuit of the instrument of FIGS. 1 and 13;

FIGS. 15a-b illustrate a schematic diagram of an electric circuit of the instrument of FIGS. 1 and 13;

FIG. 16 illustrates a reflected light signal and a rectified reflected light envelope according to the present invention;

FIGS. 17a-b illustrate enlarged fragmentary longitudinal sectional views taken generally along section lines 17--17 of FIG. 4;

FIG. 18 illustrates a detected light profile according to the present invention;

FIG. 19 illustrates two waveforms useful in understanding the start noise immunization technique employed in an instrument according to the present invention.

The following schematic and block circuit diagram descriptions identify specific integrated circuits and other components and in many cases specific sources for these. Specific terminal and pin names and numbers are generally given in connection with these for the purposes of completeness. It is to be understood that these terminal and pin identifiers are provided for these specifically identified components. It is to be understood that this does not constitute a representation, nor should any such representation be inferred, that the specific components or sources are the only components available from the same or any other sources capable of performing the necessary functions. It is further to be understood that other suitable components available from the same or different sources may not use the same terminal/pin identifiers as those provided in this description.

An instrument 100 for determining the coagulation time of a specimen, whether of blood or of a control, includes a housing 102 comprising a housing bottom 104 and a housing top 106. Top 106 is provided with a battery door 108 which covers a battery well 110 housing the instrument 100's battery power source (not shown). Bottom 104 houses a piezoelectric beeper 112, and a printed circuit board (PCB) 114 onto which are assembled various circuit components which will be described later. An optics assembly 116, a socket 118 for a test parameters electronically erasable programmable read-only memory (EEPROM) key 119 of the type described in U.S. Pat. No. 5,053,199, a socket 120 for serial data communication, and a power supply connector 122 for connection of instrument 100 to an external AC/DC adapter (not shown) for operation thereby in lieu of the batteries (not shown) with which instrument 100 is typically equipped, are also assembled onto PCB 114.

Optics assembly 116 includes a covered 126 strip adapter top assembly 132 hinged 128 to a strip adapter bottom assembly 130. Strip adapter bottom assembly 130 includes a magnet assembly 140 held to bottom assembly 130 by a spring clip retainer 142. Magnet assembly 140 includes a coil 144 wound on a bobbin 146 which is positioned over the center leg 148 of an E-core 150. The end legs 152 of E-core 150 lie outside coil 144. A bias magnet 154 is placed over the end of the center leg 148 and is supported on one end of the bobbin 146. A connector 156 permits electrical connections to be made to coil 144.

Strip adapter bottom assembly 130 also includes a sample port housing assembly 160 having a housing 162 within which are mounted a photodiode 164 and an LED 166. Photodiode 164 senses light generated by LED 166 and reflected from the sample and strip 101 to provide an indication that a sample, be it blood or control, has been applied to instrument 100 for testing. A connector 168 provides for electrical connections to photodiode 164 and LED 166. A clamp 170 retains LED 166 in housing 162. The angle between the axes of the LED 166 and photodiode 164 openings 172, 174, respectively, is about 15°.

Strip adapter bottom assembly 130 also includes a heater assembly 180 including a heater foil 182 constructed from two Kapton/WA polyamide films between which is sandwiched a copper nickel foil trace 183 having a resistance of about 13 Ω and an output power of about 2 W. A thermal fuse 184 and a thermistor 188 are mounted on the side of the foil 182 opposite the heater trace. Thermal fuse 184 is coupled through the foil 182 between one terminal 186 of the heater foil trace and the - HEATER terminal of a heater circuit. Contact is made to the leads of thermistor 188 from the THermistor + and - leads of the heater circuit through a hole 190 in the foil 182. An aluminum nitride heater plate 192 having a light reflecting top surface 194 is attached to foil 182 over the heater pattern area 193 of the heater trace using a thermosetting acrylic adhesive. Electrical connections are made to heater assembly 180 through a connector 196.

A transparent polycarbonate window 200 is adhesively attached to a region 202 of strip adapter bottom assembly housing 203 which is formed with a series of eight transversely extending slit openings 204-1-204-8, respectively. A transparent polycarbonate window 206 is provided with an opaque glossy black coating 208 over part of its surface and an opaque glossy yellow coating 210 over part of its surface. The remainder 211 of window 206 remains transparent. Remainder 211 overlies a slit 213 in housing 203 through which radiation from LED 166 is transmitted to the sample and through which remission from the sample is detected by photodiode 164. The yellow region 210 visible to the user of instrument 100 indicates where the sample, be it blood or control, is to be placed on a transparent disposable strip 101, such as those illustrated and described in U.S. Pat. No. 4,849,340 or the CoaguChek™ coagulation system test strip available from Boehringer Mannheim Corporation, 9115 Hague Road, Indianapolis, Ind. 46250, when the disposable strip 101 is properly located in the optics assembly 116. A push-button latch 214 including a button 216 biased into locking position by a scissors-shaped compression spring 218 completes strip adapter bottom assembly 130.

Strip adapter top assembly 132 includes a strip adapter top 222 into which is mounted a bar code reading photodiode 224 with an elongated active region exposed through a slot 226 and a transparent polycarbonate window 228 adhesively mounted on the underside of top 222 to close slot 226. A photosensor bracket 230 captures photodiode 224 in position adjacent slot 226. Test strip clamps containing foam springs 232, useful in pressing test strip 101 against heater plate 192, have tabs that fit into locating openings provided therefor in the floor of top 222. Space 235 is provided between clamps 232 to accommodate a positioning bracket 236 which is mounted on the underside of PCB 234 and extends downward therefrom into space 235. START LED 238 and FILL LED 240 are mounted respectively in front of and behind positioning bracket 236 angled at about 5° to the normal plane of incidence on PCB 234. A photodiode 242 with a daylight filter is mounted on PCB 234 inside positioning bracket 236. All three of components 238, 240, 242 are exposed downward through openings provided therefor in the bottom of strip adapter top 222 of the strip adapter top assembly 132. A MAIN assay LED 244 is mounted in an opening 246 provided therefor in strip adapter top 222 and is held in place by a holding clamp 248. The leads of LED 244 are connected to PCB 234. The axis of opening 246 makes an angle of about 45° with the axis of the opening for photodiode 242 and intersects it.

A pop-up bracket 250 is spring 252-loaded into an opening provided therefor in a rear end wall 254 of strip adapter top 222 to cause the strip adapter top assembly 132 to pop up when button 216 is pushed. An eleven-conductor flat cable 256 and connector 258 make the connections between the components mounted on PCB 234 and the remaining circuits of the PCB 114. Pawl-type catches 260 extend downward from the two forward corners of strip adapter top 222. Openings 262 are provided adjacent the front corners of strip adapter bottom assembly 130 to accommodate catches 260. Cooperating tongues 263 on button 216 are urged into engagement with catches 260 by spring 218 when strip adapter bottom assembly 130 and top assembly 132 are closed together. A flag 264 which extends downward from a side edge of strip adapter top 222 extends into a slot 266 provided for this purpose in strip adapter bottom assembly 130 where flag 264 interrupts a light path from a source to a detector to indicate that the strip adapter top and bottom assemblies 132, 130, respectively, are closed together.

The electrical circuitry on PCB 114 powers and reads the various sensors included on the coagulation optics circuit 270 on PCB 234. +5V and -5V are supplied to circuit 270 through terminals 258-5 and 258-1, respectively, of connector 258. Unregulated voltage is supplied to terminal 258-8 of connector 258. Ground for circuit 270 is provided at terminals 258-2, 4 and 7 of connector 258. A capacitor is coupled across terminals 258-8 and 258-2, 4, 7. The anodes of LEDs 238, 240, 244 are all coupled to terminal 258-8. The cathode of LED 238 is coupled to the START terminal, terminal 258-11, of connector 258. The cathode of LED 240 is coupled to the FILL terminal, terminal 258-10, of connector 258. The cathode of LED 244 is coupled to the MAIN terminal, terminal 258-9, of connector 258.

The anodes of photodiodes 224, 242 are coupled through a resistor 273 to terminal 258-1. The cathode of photodiode 242 is coupled to the - input terminal of an operational amplifier 274. The + input terminal of operational amplifier 274 is coupled to the anodes of photodiodes 224, 242. The output terminal of operational amplifier 274 is coupled to its - input terminal through a parallel RC feedback circuit. The output terminal of operational amplifier 274 is also coupled to the DETect terminal, terminal 258-3, of connector 258.

The cathode of photodiode 224 is coupled to the - input terminal of an operational amplifier 278. The + input terminal of operational amplifier 278 is coupled to the anodes of photodiodes 224, 242. The output terminal of operational amplifier 278 is coupled to its - input terminal through a parallel RC feedback circuit. The output terminal of differential amplifier 278 is also coupled to the CodeBaR OUTput terminal, terminal 258-6, of connector 258.

A +V terminal of a 2.5V reference voltage source 279 is coupled to terminals 258-2, -4 and -7 of connector 258. The - terminal of reference voltage source 279 is coupled to the anodes of photodiodes 224, 242, to the + input terminals of operational amplifiers 274, 278, and through resistor 273 to the -5V terminal, 258-1, of connector 258.

The electric circuitry 280 mounted on PCB 114 processes the various signals from circuitry 270, as well as others which circuitry 280 generates itself or receives from the user of instrument 100, or which are generated externally to instrument 100. An Intel type N83C51FC eight-bit microcontroller (μC) 284 has data terminals P0.0-P0.7 coupled to DATA lines 0-7, respectively, of an instrument 100 bus 286. μC 284 address terminals P2.0-P2.4 and P2.6-P2.7 are coupled to address lines A8-A12 and A14-A15, respectively, of bus 286. The ReaD and WRite terminals, P3.7 and P3.6, respectively, of μC 284, are coupled to the Read Data and Write Data lines, respectively, of bus 286. An Address Latch Enable terminal of μC 284 is coupled to the ALE terminal of a Toshiba type TC11L003AU-1031 application specific programmable gate array integrated circuit (ASIC) 290. The TIP (transmit) terminal 120-2 of serial data port socket 120 is coupled through the parallel combination of a capacitor and a resistor to ground, and through a series resistor to the Transmit Data (TXD) terminal P3.1 of μC 284. The RING (receive) terminal 120-3 of serial data port socket 120 is coupled through the parallel combination of a capacitor and a resistor to ground and through a series resistor to the Receive Data (RXD) terminal P3.0 of μC 284. The GrouND terminal 120-1 of socket 120 is coupled to ground.

The CS terminal 118-1 of ROM key socket 118 is coupled through a 6.2V Zener diode to ground and directly to a Code ROM IC chip Select OutPut terminal 22 of ASIC 290. The SK terminal, 118-2, of ROM key socket 118 is coupled through a Zener diode to ground and directly to the CLOCK terminal, terminal P1.0, of μC 284. It is also coupled to the SK terminal of an EEPROM 292 internal to instrument 100. EEPROM 292 generally contains the meter 100 characterizing parameters. The DI and DO terminals, terminals 118-3 and 4, of socket 118 are coupled to each other, to ground through a Zener diode, directly to the DI and DO terminals of EEPROM 292, and directly to the EEDI/DO terminal P3.5, of μC 284. Terminal 118-5 of socket 118 is coupled to ground. Terminal 118-8 of socket 118 is coupled to the system +5V supply.

The time base for μC 284 is generated by a 7.3728 MHz crystal which is coupled across terminals X1-X2 thereof. A capacitor is coupled between each terminal of the crystal and ground. Terminal P1.5 of μC 284 is coupled to a resistive voltage divider in a beeper 112 driver circuit 294. The common terminal of the series resistors is coupled to the base of a driver transistor 296. The collector of transistor 296 is coupled through a pull-up resistor to +5V and directly to one terminal of beeper 112. The emitter of transistor 296 and the other terminal of beeper 112 are both coupled to ground. Two diodes clamp the collector of transistor 296 between ground and +5V.

The data terminals D0-D7 of a 8K by 8 static random access memory (SRAM) 300 are coupled to the DATA 0-DATA 7 lines, respectively, of bus 286. The address terminals A0-A12 of SRAM 300 are coupled via the system bus 286 to the A0-A7 terminals of ASIC 290 and the A8-A12 terminals of μC 284, respectively. The ReaD and WRite terminals of SRAM 300 are coupled via the bus 286 to the ReaD and WRite terminals, respectively, of μC 284. The CE2 terminal of SRAM 300 is coupled to the junction of a resistor and a capacitor. The other terminal of the resistor is coupled to +5V. The other terminal of the capacitor is coupled to ground. The CE2 terminal is clamped via a diode to +5V. The DATA 0-DATA 7 terminals of a two line by sixteen character display 302 are coupled to the DATA 0-DATA 7 terminals of bus 286. The DISPlay ENable terminal of display 302 is coupled via bus 286 to the DISPlay ENable terminal of ASIC 290. The A0-A1 terminals of display 302 are coupled to the A0-A1 terminals, respectively, of bus 286. The GrouND terminal of display 302 is coupled to the system ground and the VDD terminal of display 302 is coupled to +5V. Terminal 3 of display 302 is coupled through a resistor to ground and through a resistor to +5V. An instrument 100 keypad switch has its ON/OFF terminal connected to the source of a field effect transistor (FET) 303 in instrument 100's power supply circuit 304. The YES terminal of the switch is coupled to InPut terminal 1 of ASIC 290. The NO terminal of the switch is coupled to InPut terminal 2 of ASIC 290. The YES and NO terminals are also coupled through respective pull-up resistors to +5V.

Battery back-up protection is provided to SRAM 300 by a circuit including a 3.3V regulator 306. The V_(in) terminal of regulator 306 is coupled to the junction of a resistor and a capacitor. The other terminal of the capacitor is coupled to ground. The other terminal of the resistor is coupled to the cathode of a diode, the anode of which is coupled to +VBAT. The V_(out) terminal of regulator 306 is coupled across a series resistive voltage divider including a resistor 308 and a resistor 310 to ground. V_(out) is also coupled to the emitter of a transistor 312. The junction of resistors 308, 310 is coupled to the base of a transistor 314. The emitter of transistor 314 is coupled to ground. Its collector is coupled through a series resistor to the base of transistor 312. The collector of transistor 312 is coupled to the BATtery 1 terminal of a real time clock 316, and to one terminal of a capacitor, the other terminal of which is coupled to ground. The D and Q terminals of IC 316 are coupled to the DATA 0 line of bus 286. The CEI, CEO, WE and OE terminals of IC 316 are coupled to terminal P2.7(A15) of μC 284, terminal CE of SRAM 300, the Write Data line of bus 286, and the Read Data line of bus 286, respectively. The VCC OUTPUT terminal of IC 316 is coupled to the VDD terminal of SRAM 300 and through a capacitor to ground. The time base for IC 316 is generated by a 32.768 KHz crystal coupled across terminals X1-X2 thereof.

The PoWeR INTerrupt, MAIN ConTroL, HeaTeR ON/OFF, A/D OUT, A/D A, A/D B, power SUPPLY ON, SAMPLE ConTroL, and MAGnet 1 ConTroL terminals, terminals P3.2, P3.3, P3.4, P1.1, P1.2, P1.3, P1.4, P1.6 and P1.7, respectively of μC 284, are coupled to the power supply circuit 304, the main LED driver in an LED driver circuit 320, the heater control circuit 322, the COMParator OUTput terminal of a Teledyne type TSC500ACOE A/D converter IC 324 in the analog section of instrument 100, the A terminal of A/D 324, the B terminal of A/D 324, power supply circuit 304, the sample port circuit 326, and the magnet current control circuit 328.

The InPut 3 terminal of ASIC 290 is coupled to an optical switch 486. The OutPut 10-17 terminals of ASIC 290 are coupled to the bar code LED array driver circuit 330. The OutPut terminals 20, 21, 24 and 25 of ASIC 290 are coupled to the setpoint temperature control of heater driver circuit 322, the LATCH ENABLE terminal of an eight-to-one analog multiplexer 332 in the analog section of instrument 100, the fill LED driver in circuit 320, and the start LED driver in circuit 320, respectively. The Address 0-2 lines of bus 286 are coupled to the A, B and C terminals, respectively, of multiplexer 332.

Power supply circuit 304 includes an instrument 100 battery connector 334 having +VBAT terminal 334-1 and ground terminal connector 334-2 and AC/DC converter power supply connector 122 having +VIN terminals 122-3 and 6 connected together and GRouNd terminals 122-1 and 4 connected together. +VBAT is coupled through a series resistor to the gate of FET 303. The drain of FET 303 is coupled through two series resistors 336, 338 to the base of a transistor 340. The emitter of transistor 340 is coupled to its base through the series combination of a resistor and a diode, through a diode and 2.0 ampere fuse to +VIN, and through a parallel combination of a transient suppressor diode, a resistor and a capacitor to ground. The junction of resistors 336, 338 is coupled through a resistor to the base of a transistor 342. The emitter of transistor 342 is coupled to the base of transistor 340. The collector of transistor 342 is coupled through two series resistors to ground. The common terminal of these resistors is coupled to the base of a transistor 346. The emitter of transistor 346 is coupled to ground and its collector is coupled through a pull-up resistor to +5V. The collector of transistor 346 is also coupled to InPut terminal 0 of ASIC 290.

The emitter of a transistor 350 is coupled to +VBAT. +VBAT is coupled through a resistor and a diode in series to the base of transistor 350. The base of transistor 350 is coupled through a diode 351 to the base of transistor 340. The base of transistor 340 is coupled through a parallel resistance network to the collector of a transistor 352. The emitter of transistor 352 is coupled to ground. Its base is coupled through a resistor to ground and through a resistor to the collector of a transistor 354. The emitter of transistor 354 is coupled to +5V Analog. The base of transistor 354 is coupled through a resistor to +5VA. The base of transistor 354 is also coupled through a resistor to terminal P1.4 of μC 284. Once the on/off key to meter 100 is depressed upon turn-on, enough time is given for the +5V supply to come up and the μC 284 to reset itself (once +5V supply has been applied to its VCC pin) and then to have terminal P1.4 of μC 284 latch the system +5V supply on. This terminal is also used to shut the system down in an orderly fashion. VUNREGulated appears at the collector of transistor 350 and at the cathode of a diode 356, the anode of which is coupled to the collector of transistor 340.

Regulation is initiated by battery voltage +VBAT on the gate of FET 303. If the battery is in backward, or is below minimum regulation level and no AC/DC adapter is connected to instrument 100, or is missing and no AC/DC adapter is connected to instrument 100, the instrument 100 cannot be turned on. If the battery is installed properly and is above minimum regulation level, regulation is established at the base of transistor 340 and, through diode 351, at the base of transistor 350. Regulation is also signalled through transistors 342 and 346 to the ON/OFF INDicator InPut terminal 0 of ASIC 290. If the battery voltage +VBAT is greater than +VIN, diode 356 decouples the AC/DC adapter input circuity, including transistor 340 and its associated regulating circuitry from VUNREGulated so that the battery does not power that circuitry.

VUNREGulated is supplied to the VIN terminal of a +5V regulator IC 360. VUNREGulated is also supplied to a series voltage divider including a resistor 362 and a resistor 364. The common terminal of resistors 362, 364 is coupled to the INput terminal of a voltage detector IC 366. The ERROR output terminal of IC 366 is coupled through a resistor to VUNREGulated and through a resistor to the base of a transistor 368. The collector of transistor 368 is coupled through a load resistor to VUNREGulated and is coupled directly to the SHUTDOWN terminal of +5V regulator IC 360. If the supply voltage is low, IC 366 will prevent instrument 100 from being turned on. Regulated +5V for the digital circuitry of instrument 100 appears at the VOUT terminal of +5V regulator IC 360. The SENSE terminal of IC 360 is coupled to +5V. The ERROR terminal of IC 360 is coupled through a pull up resistor to +5V. The ERROR terminal is also coupled to the PoWeRINTerrupt terminal, P3.2, of μC 284. The error terminal's main function is to warn the μC 284 that the system power is approaching an unregulated condition. By warning μC 284 of such condition, μC 284 can power down the system in an orderly fashion prior to any soft failures occurring. A capacitor across VOUT and GrouND of IC 360 is decoupled by a resistor from a tantalum capacitor across the +5 VAnalog supply to analog ground. The voltage across the VOUT output terminal to ground is fed back through a diode and resistor in series to the base of transistor 368. The VOUT output terminal of IC 360 is also coupled to the V+ terminal of a +5V-to--5V converter 369. A tantalum capacitor is coupled across the CAP+ and CAP- terminals of converter 369. -5VDC for circuits requiring it appears across the VOUT terminal of converter 369 to ground. The instrument 100's analog and digital grounds are tied together here. A +V terminal of an 2.5V reference voltage source 370 is coupled through a resistor to +5 VAnalog. 2.5 VREFerence is established across the +V terminal of source 370 and ground.

Turning now to the LED driver circuitry 320 for the optical head assembly 116, the start LED control OutPut terminal 25 of ASIC 290 is coupled through a diode to the - input terminal of an operational amplifier 374. The + input terminal of operational amplifier 374 is coupled to VREF. The output terminal of operational amplifier 374 is coupled to the base of a transistor 376. The collector of transistor 376 is coupled to the START LED terminal, terminal 258-11, of connector 258. The emitter of transistor 376 is coupled to ground through a resistor, which limits the current through the start LED at a constant current, and through a feedback resistor to the - input terminal of operational amplifier 374.

The FILLConTroL terminal, OutPut terminal 24, of ASIC 290 is coupled through a diode to the - input terminal of an operational amplifier 378. The + input terminal of operational amplifier 378 is coupled to VREF. The output terminal of operational amplifier 378 is coupled to the base of a transistor 380, the collector of which is coupled to the FILL LED terminal, terminal 258-10, of connector 258. The emitter of transistor 380 is coupled through a parallel resistor network to ground, which limits the current through the fill LED at a constant current, and through a feedback resistor to the - input terminal of operational amplifier 378.

The MAIN ConTroL terminal, P3.3, of μC 284 is coupled through a diode to the - input terminal of an operational amplifier 382. The + input terminal of operational amplifier 382 is coupled to VREF. The output terminal of operational amplifier 382 is coupled to the base of a Darlington-coupled transistor pair 384. The collectors of transistors 384 are coupled to the MAIN assay LED terminal, 258-9, of connector 258. The emitter of transistors 384 is coupled through a resistor to ground, which limits the current through the main LED at a constant current, and through a resistor, to the - input terminal of operational amplifier 382.

The sensed bar code of the disposable test strip 101 which is being used in a particular test comes in to circuit 320 serially on the CodeBaR terminal, 258-6, of connector 258. It is coupled directly to analog input terminal X5 of multiplexer 332. The START, FILL and MAIN assay DETect signals indicating that an adequate volume sample droplet has been placed over yellow area 210 on a test strip 101, and its raw coagulation results data, are provided from terminal 258-3 of connector 258 to the + input terminals of two operational amplifiers 386, 388. Operational amplifier 386 is configured as a unity gain buffer and its output terminal is coupled to the DC input terminal X1 of multiplexer 332. Operational amplifier 388 is also configured as a unity gain buffer and its output terminal is capacitively coupled through a capacitor and two series resistors 390, 392 to a + input terminal of an operational amplifier 394. The output terminal of operational amplifier 388 is also coupled to ground through an RC parallel combination. The + terminal of operational amplifier 394 is coupled to ground through a capacitor. The output terminal of operational amplifier 394 is coupled through a feedback resistor to its - input terminal. Its - input terminal is coupled to ground through a resistor. The output terminal of operational amplifier 394 is also coupled through series resistors 396, 398 to ground. The common terminal of resistors 396, 398 is coupled through a capacitor to the common terminal of resistors 390, 392.

The signal at the output terminal of operational amplifier 394 is directly coupled to the X0 input terminal, AC1, of multiplexer 332. That signal is also coupled to the + input terminal of an operational amplifier 400. The signal at the output terminal of operational amplifier 400 is directly coupled to the X2 input terminal, AC2, of multiplexer 332. The output terminal of operational amplifier 400 is also coupled through a resistor to the - input terminal thereof. The - input terminal of operational amplifier 400 is coupled through a resistor to ground.

VUNREGulated is coupled through a series voltage divider including a 324KΩ, 1% resistor 402 and a 124KΩ, 1% resistor 404 to ground. The common terminal of resistors 402, 404 is coupled directly to the analog BATTery voltage input terminal X4 of multiplexer 332. +5VA is coupled to the VDD input terminal of a Seiko type S8100BF temperature sensor 406. The VOUT terminal of sensor 406 is coupled directly to the analog VTEMP voltage input terminal, X6, of multiplexer 332 and through a 1MΩ pull-up resistor to +5VA.

The heater control circuit 322 includes two series 100KΩ resistors 410, 412 coupled between the HeaTeR ON/OFF terminal of μC 284 and ground. The common terminal of resistors 410, 412 is coupled to the base of a type BC848C NPN transistor 414, the collector of which is coupled through two series 100KΩ resistors 416, 418 to +5VA, and the emitter of which is coupled to ground. The common terminal of resistors 416, 418 is coupled to the base of a type BC858C PNP transistor 420, the emitter of which is coupled to +5VA, and the collector of which is coupled through a series 10KΩ, 1% resistor 422 and 120 pF capacitor 424 to ground. The common terminal of resistor 422 and capacitor 424 is coupled to the - input terminal of a type LM324A operational amplifier 426.

+5VA is coupled through a series 100KΩ, 1% resistor, a 2KΩ, ten turn potentiometer 428 and a 3.48KΩ, 1% resistor to ground. The movable contact of potentiometer 428 is coupled to the - input terminal of operational amplifier 426. The potentiometer enables the heater plate 192 to achieve about 39° C. +5VA is coupled through a series 100KΩ, 1% resistor 430 and 120 pF capacitor 432 to ground. The common terminal of resistor 430 and capacitor 432 is coupled to the THermistor + terminal, 196-3, of connector 196, and to the + input terminal of operational amplifier 426. The + input terminal of operational amplifier 426 is coupled through the series combination of a type LL4148 diode and a 100KΩ resistor to ground. The junction of the resistor and diode is coupled to the base of a type BC848C NPN transistor 434, the emitter of which is coupled to ground. The output terminal of operational amplifier 426 is coupled through a 1MΩ, 1% resistor to its - input terminal and through the series combination of a type LL4148 diode and a 200Ω resistor to the collector of transistor 434.

The SETPoinT 2 terminal, OutPut terminal 20, of ASIC 290, is coupled through series 100KΩ resistors 436, 438 to +5VA. The ASIC 290 provides control of the heater plate 192 temperature at two different setpoints, 39° C. and 44° C. The second setpoint is set high to permit the heater plate 192 to attain 44° C. temperature, thereby permitting more rapid warming of samples to 39° C. The common terminal of resistors 436, 438 is coupled to the base of a type BC858C PNP transistor 440, the emitter of which is coupled to +5VA and the collector of which is coupled through a 348KΩ, 1% resistor to the - input terminal of operational amplifier 426. A series resistive voltage divider including a 249KΩ, 1% resistor 442 and a 1MΩ, 1% resistor 444 is coupled between the output terminal of operational amplifier 426 and ground. The common terminal of resistors 442, 444 is coupled to an analog input terminal X3 of multiplexer 332. Heater control circuit 322 operating status is thus multiplexed into μC 284. Additionally, heater control status, as reflected by the voltage at the collector of transistor 434, controls the flow of current through the heater foil 182. This is accomplished through a Samsung type MJD3055 NPN transistor 446, the base of which is coupled to the collector of transistor 434 and the collector of which is coupled to the - HEATER terminal, 196-2, of connector 196. The + HEATER terminal, 196-1, of connector 196 is coupled to + VUNREGulated. The emitter of transistor 446 is coupled through a parallel resistance network having an effective resistance of about 1.5Ω to ground. The base of transistor 446 is also coupled through two series type LL4148 diodes to ground, which limits the current through the heater foil to approximately 0.4A. The - THermistor terminal, 196-4, of connector 196 is coupled to ground.

Thus, an instrument 100 for determining a characteristic, such as a coagulation time, of a biological fluid, such as blood, or a control comprises a slide 101 defining a cuvette 494, 510 for receiving a sample 514 of the biological fluid or control the characteristic of which is to be determined in such a way that the characteristic is exhibited by the sample 514. The sample 514 is monitored (FIG. 16) as the characteristic is exhibited, and a result of the monitoring of the sample 514 is converted by the circuit of FIGS. 15a-b into the characteristic. A heater 180 is provided for heating the sample 514 and for maintaining the temperature of the sample 514 at about a first temperature (39° C.). A control 322 controls the heater. The heater comprises a heater element 182, a support 192 for supporting the heater element 182 in heat conducting relationship 494, 510, 506 to the sample 514 when the instrument 100 is in use, a thermistor 188 for monitoring a temperature of the support 192, and means FIG. 7a for mounting the thermistor 188 adjacent the support 192. The heater control 322 comprises a first temperature setpoint control 428 for controlling the heater 180 to maintain the temperature of the sample 514 at about the first temperature (39° C.) and a second temperature setpoint control (SETPoinT 2 terminal, OutPut: terminal 20, of ASIC 290) for overriding the first temperature setpoint control 428 to heat the sample 514 toward a second temperature (44° C.), means (196-3, 196-4, THermistor + and - leads) for coupling the thermistor 188 to the heater control 322, and means (196-1, 196-2, HEATER + and - leads) for coupling the heater element 182 to the heater control 322.

The instrument 100 comprises a controller 290 and the second temperature setpoint control comprises an output terminal (SETPoinT 2 terminal, OutPut terminal 20, of ASIC 290) of the controller 290 for providing a signal that the support means 192 is to be heated from ambient temperature for determining the characteristic of the biological fluid or control.

The heater control 322, the thermistor 188 and the means (196-3, 194-4, THermistor + and - leads) for coupling the thermistor 188 to the heater control 322 together comprise a differential amplifier 426 and a bridge circuit having first (420, 422), second (potentiometer 428, resistor to ground), third (430) and fourth (196-3, 196-4, THermistor + and - leads and thermistor 188) bridge legs. The differential amplifier 426 includes an inverting input terminal coupled to the wiper of potentiometer 428 and a non-inverting input terminal (junction of resistor 430 and capacitor 432), conductors for coupling the inverting input terminal and the first (420, 422) and second (potentiometer 428, resistor to ground) legs of the bridge together, and conductors for coupling the non-inverting input terminal (junction of resistor 430 and capacitor 432) and the third (430) and fourth (196-3, 196-4, THermistor + and - leads and thermistor 188) legs of the bridge together. The second leg of the bridge includes the first temperature setpoint control 428 and the fourth leg of the bridge includes the thermistor 188.

The first temperature setpoint control comprises a potentiometer 428 for setting the temperature (39° C.) at which the support 192 is to be maintained during the reaction.

The heater element 182 and the support 192 together comprise an electrically resistive film pattern 183 supported on a ceramic tile 192. The tile 192 has a first surface FIG. 7b on which the electrically resistive film pattern 183 is provided.

The ceramic tile 192 illustratively comprises an aluminum nitride tile.

The ceramic tile 192 comprises a second surface 194 opposite the first surface FIG. 7b. The characteristic of the biological fluid or control is determined by placing the sample 514 into a cuvette 494, 510 having a third surface 506 for bringing into heat conducting relationship with the second surface 194 of the ceramic tile 192 prior to determination of the characteristic.

Terminal P1.6 of μC 284 is coupled through a diode to the - input terminal of an operational amplifier 450 in the sample port circuit 326. The + input terminal of operational amplifier 450 is coupled to VREF. The output terminal of operational amplifier 450 is coupled to the base of a transistor 452, the emitter of which is coupled through a feedback resistor to the - input terminal of operational amplifier 450 and to ground through resistance, which limits the current through the sample port LED at a constant current. The collector of transistor 452 is coupled to terminal 168-1 of the sample port connector 168. +5VA is coupled to terminal 168-2, the VDD terminal, of connector 168. VUNREGulated is coupled to terminal 168-5 of connector 168. The SAMPle IN terminal, 168-4, of connector 168 is coupled to ground through a resistor and through a capacitor to the - input terminal of an operational amplifier 456. The + input terminal of operational amplifier 456 is coupled to ground. The output terminal of operational amplifier 456 is coupled through a parallel RC feedback circuit to its - input terminal. The output terminal of operational amplifier 456 is coupled through a capacitor to the + input terminal of an operational amplifier 458. The + input terminal of operational amplifier 458 is coupled to ground through a resistor.

The - input terminal of operational amplifier 458 is coupled to ground through a resistor. The output terminal of operational amplifier 458 is coupled to the cathode of a diode, the anode of which is coupled through a resistor to the - input terminal of operational amplifier 458. The output terminal of operational amplifier 458 is also coupled to the anode of a diode 460, the cathode of which is coupled through a resistor 462 to the - input terminal of operational amplifier 458. This provides a hysteresis-type configuration which has different gains depending upon whether the voltage at the + input terminal of operational amplifier 458 is greater than or less than the voltage at the - input terminal thereof. The common terminal of diode 460 and resistor 462 is coupled through the series combination of a resistor 464 and a capacitor 466 to ground. The common terminal of resistor 464 and capacitor 466 is coupled to the SAMPle DETect input terminal, X7, of multiplexer 332.

Terminal P1.7 of μC 284 is coupled through two series resistors in the magnet control circuit 328 to ground. The common terminal of these resistors is coupled to the base of a transistor 470, the emitter of which is coupled to ground. The collector of transistor 470 is coupled through series resistors to +5VA. The common terminal of these resistors is coupled to the base of a transistor 471, the emitter of which is coupled to +5VA and the collector of which is coupled to the - input terminal of an operational amplifier 472. The series combination of a resistor 474 and a resistor 476 is coupled between VREF and ground. A capacitor is coupled across resistor 476. The common terminal of resistors 474 and 476 is coupled to the + input terminal of operational amplifier 472.

The output terminal of operational amplifier 472 is coupled to the base of a magnet coil 144-driver transistor 478. The emitter of transistor 478 is coupled through a resistor to ground, which limits the current through the magnet coil at a constant current, and through a feedback resistor to the - input terminal of operational amplifier 472. A capacitor is coupled between the - input terminal of operational amplifier 472 and ground. The collector of transistor 478 is coupled to terminal 156-3 of connector 156. Terminal 156-1 of connector 156 is coupled to VUNREGulated. Coil 144 is coupled across connectors 156-1 and 156-3. The series combination of a resistor and a capacitor is also coupled across connectors 156-1 and 156-3. A flyback diode is also coupled across terminals 156-1 and 156-3.

The bar code LED driver circuit 330 which is associated with photodiode 224 includes eight bar code-illuminating LEDs 484-1-484-8. The anode of LED 484-1 is coupled to +5V and its cathode is coupled to the Anode terminal of optical switch 486. Optical switch 486 provides the source and detector for flag 264 to indicate when the strip adapter top and bottom assemblies 130, 132 are closed together. The collector terminal, C, of optical switch 486 is coupled to InPut terminal 3 of ASIC 290, and through a load resistor to +5V. The cathode terminal, K, of optical switch 486 is coupled through a load resistor to the collector of a transistor 490-1, the emitter of which is coupled to ground and the base of which is coupled through a resistor to OutPut terminal 17 of ASIC 290. The anodes of the remaining LEDs 484-2-484-8 are coupled through a common load resistance to +5V. The cathodes of LEDs 484-2-484-8 are coupled to the collectors of transistors 490-2-490-8, respectively. The emitters of transistor 490-2-490-8 are coupled to ground. The bases of transistor 490-2-490-8 are coupled through respective resistors to OutPut terminals 16-10, respectively, of ASIC 290.

LEDs 484-1-484-8 are mounted on PCB 114 and emit light through respective slit openings 204-1-204-8, respectively. LED's 484-1-484-8 are sequentially energized through transistors 490-1-490-8, respectively. The presence or absence of a bar code in region 492 of a particular test strip 101 placed in instrument 100 is sensed by transmission of light from a respective LED 484-1-484-8 by conduction of photodiode 224. This identifies certain test strip 101 lot-specific parameters for instrument 100.

In operation, a sample 514 is deposited in the test strip 101 sample well 494 over location 210. Radiation from LED 164, which is strobed at 0.25 sec. intervals, detected by photodiode 166 establishes the dosing of strip 101. START LED 238 is strobed at 50 msec. intervals until the arrival of the sample 514 at the region of strip 101 over START LED 238 is established by the radiation from START LED 238 detected by photodiode 242. The flow time of the sample 514 between the sample application point at well 494 and the detection of the arrival of the sample 514 over the START LED 238 establishes the sample 514 as blood or a control. The control solutions, being less viscous, flow between these two locations more rapidly, and this is detected by the instrument 100. The minimum flow time that the instrument 100 will interpret as blood and/or the maximum flow time that the instrument 100 will interpret as control can be varied from strip lot to strip lot by changing (a) parameter(s) in the user-insertable EEPROM key 119. This relieves the user from the need to indicate to the instrument 100 or otherwise record when a quality control check is being conducted.

After photodiode 242 has detected the arrival of the sample 514 over the START LED 238, the START LED 238 is deenergized and the FILL LED 240 is energized. The next decrease in radiation detected by photodiode 242 indicates the arrival of the sample 514 over the FILL region of the strip 101. The elapsed time between detection by photodiode 242 of arrival of the sample 514 over START LED 238 and detection by photodiode 242 of arrival of the sample 514 over FILL LED 240 is used by the instrument 100 to determine whether the volume of the sample 514 which was applied is adequate to conduct a coagulation test. If the instrument 100 determines that the applied sample 514 volume was inadequate to conduct a test, the instrument 100 provides an error message and returns to its ready state. If the instrument 100 determines that the applied sample 514 volume was sufficient to conduct a coagulation time test reliably, FILL LED 240 is deenergized and MAIN assay LED 244 is energized. Electromagnet 140 is also energized and monitoring by photodiode 242 of MAIN assay LED 244 radiation begins. Magnet assembly 140, when driven by magnet current control circuit 328, stirs ferromagnetic particles from the test strip 101 borne by the sample 514, be it blood or control. The particles reorient themselves along the combined lines of force of magnet assembly 140 and bias magnet 154 and provide a modulated light transmission profile of the sample. This transmission profile, illustrated in FIG. 16 at 500, is detected by photodiode 242 and is multiplexed (DETect--AC1-DC) via multiplexer 332 and A/D 324 into μC 284. Coagulation of the sample causes the reduction in the modulation in this transmission profile as described in U.S. Pat. Nos. 4,849,340 and 5,110,727. Waveform 500 is rectified and the envelope 502 of the rectified waveform 500 is formed.

To reduce the likelihood of double dosing the strip 101, the ratio of START to FILL time-to-sample application to START time is formed. This ratio is compared to a parameter provided from key 119. The ratio must be less than the parameter. Otherwise the instrument 100 will conclude that the strip 101 has been double dosed and will generate an error message. Double dosing is to be avoided because it can refluidize the ferromagnetic particles, producing an erroneous coagulation time reading.

FIGS. 17a-b are much-enlarged fragmentary longitudinal sectional views of a strip 101 taken along section lines 17--17 of FIG. 4. Generally, in the absence of liquid blood, a blood fraction or control (FIG. 17a), the indices of refraction of the strip bottom 506 and top 508 and the air-filled sample volume 510 between them are such that the level of light from LED 164 returning to photodiode 166 is relatively higher. This is illustrated at region 512 of FIG. 18. A liquid sample 514, be it blood, a blood fraction or a control, is deposited into the sample well 494 of strip 101 and migrates into region 510 of strip 101 over region 211 of instrument 100. Owing generally to the matching of the strip bottom 506's, top 508's and liquid 514's indices of refraction and absorption in the case of clear liquids, and generally to absorption and scattering effects in the case of whole blood, a relatively lower light level is detected by photodiode 166 as illustrated at region 522 in FIG. 18 when a liquid is present on strip 101 adjacent region 211. This optical detection scheme permits a clear control to be used.

FIG. 19 illustrates two waveforms useful in understanding the start noise immunization technique employed in an instrument according to the present invention. It has been experimentally determined that, unless provisions are made in instrument 100 to prevent it, instrument 100 can be falsely triggered by negative-going noise spikes 526 that are generated during application of a sample to a test strip 101. Such spikes 526 are caused when the user accidentally taps or moves the strip 101 from side to side or in and out of the optics assembly 116 during sample application. Such negative-going spikes 526 can be greater than the instrument 100's -60 mV starting threshold, but are typically shorter in duration than the negative-going start signal 528 and are preceded or followed immediately by positive-going spikes 530. This is in contrast to the actual liquid sample signal 528 which is only negative-going. This difference is used to discriminate effectively between signal 528 and noise 526, 530. The instrument 100's START algorithm discriminates between short (noise) 526, 530 and long (start signal) 528 duration signals using negative trend, rate of signal change and negative threshold criteria. The flow of the START algorithm includes the following illustrative characteristics: three consecutive data points sampled 50 msec apart must be negative relative to a reference and have rates of signal change more negative than -7.3 mV/50 msec (-30 counts of the A/D converted input signal at 0.243 mV/count) with an absolute signal change more negative than the -60 mV (-246 counts) instrument 100 start threshold. The parameters stored in the EEPROM 119 then would include a signal delta of -30 counts and a start threshold of -246 counts. 

What is claimed is:
 1. An instrument for determining a characteristic of a biological fluid or a control, the instrument comprising means for receiving a sample of the biological fluid or control, the characteristic of which is to be determined, in such a way that the characteristic is exhibited by the sample, means for monitoring the sample as the characteristic is exhibited, means for converting a result of the monitoring of the sample into the characteristic, a heater for heating the sample and for maintaining the temperature of the sample at about a first temperature and a control for controlling the heater, the heater comprising a heater element, means for supporting the heater element in heat conducting relationship to the sample when the instrument is in use, means for monitoring a temperature of the support means, means for mounting the means for monitoring the temperature of the support means adjacent the support means, the heater control comprising a first temperature setpoint control for controlling the heater to maintain the temperature of the sample at about the first temperature and a second temperature setpoint control for overriding the first temperature setpoint control to heat the sample toward a second temperature, means for coupling the monitoring means to the heater control, and means for coupling the heater element to the heater control.
 2. The system of claim 1 wherein the instrument comprises a controller and the second temperature setpoint control comprises an output terminal of the controller for providing a signal that the support means is to be heated from ambient temperature for determining the characteristic of the biological fluid or control.
 3. The system of claim 2 wherein the heater control, the monitoring means and the means for coupling the monitoring means to the heater control together comprise a differential amplifier and a bridge circuit having first, second, third and fourth bridge legs, the differential amplifier including an inverting input terminal and a non-inverting input terminal, means for coupling the inverting input terminal and the first and second legs of the bridge together, and means for coupling the non-inverting input terminal and the third and fourth legs of the bridge together, the second leg of the bridge including the first temperature setpoint control and the fourth leg of the bridge including the means for monitoring the temperature of the support means.
 4. The system of claim 3 wherein the means for monitoring the temperature of the support means comprises a temperature sensitive element.
 5. The system of claim 3 wherein the first temperature setpoint control comprises a potentiometer for setting the temperature at which the support means is to be maintained during the reaction.
 6. The system of claim 1 wherein the heater element and the means for supporting the heater element together comprise an electrically resistive film pattern supported on a ceramic tile, the tile having a first surface on which the electrically resistive film pattern is provided.
 7. The system of claim 6 wherein the ceramic tile comprises an aluminum nitride tile.
 8. The system of claim 7 wherein the ceramic tile comprises a second surface opposite the first surface, the characteristic of the biological fluid or control being determined by placing the sample into a cuvette having a third surface for bringing into heat conducting relationship with the second surface of the ceramic tile prior to determination of the characteristic.
 9. The system of claim 8 wherein the means for monitoring the temperature of the support means comprises a thermistor.
 10. The system of claim 6 wherein the ceramic tile comprises a second surface opposite the first surface, the characteristic of the biological fluid or control being determined by placing the sample into a cuvette having a third surface for bringing into heat conducting relationship with the second surface of the ceramic tile prior to determination of the characteristic.
 11. The system of claim 10 wherein the means for monitoring the temperature of the support means comprises a thermistor.
 12. The system of claim 10 wherein the instrument comprises a controller and the second temperature setpoint control comprises an output terminal of the controller for providing a signal that the support means is to be heated from ambient temperature for determining the characteristic of the biological fluid or control.
 13. The system of claim 12 wherein the heater control, the monitoring means and the means for coupling the monitoring means to the heater control together comprise a differential amplifier and a bridge circuit having first, second, third and fourth bridge legs, the differential amplifier including an inverting input terminal and a non-inverting input terminal, means for coupling the inverting input terminal and the first and second legs of the bridge together, and means for coupling the non-inverting input terminal and the third and fourth legs of the bridge together, the second leg of the bridge including the first temperature setpoint control and the fourth leg of the bridge including the means for monitoring the temperature of the support means.
 14. The system of claim 13 wherein the means for monitoring the temperature of the support means comprises a temperature sensitive element.
 15. The system of claim 13 wherein the first temperature setpoint control comprises a potentiometer for setting the temperature at which the support means is to be maintained during the reaction.
 16. The system of claim 6 wherein the instrument comprises a controller and the second temperature setpoint control comprises an output terminal of the controller for providing a signal that the support means is to be heated from ambient temperature for determining the characteristic of the biological fluid or control.
 17. The system of claim 16 wherein the heater control, the monitoring means and the means for coupling the monitoring means to the heater control together comprise a differential amplifier and a bridge circuit having first, second, third and fourth bridge legs, the differential amplifier including an inverting input terminal and a non-inverting input terminal, means for coupling the inverting input terminal and the first and second legs of the bridge together, and means for coupling the non-inverting input terminal and the third and fourth legs of the bridge together, the second leg of the bridge including the first temperature setpoint control and the fourth leg of the bridge including the means for monitoring the temperature of the support means.
 18. The system of claim 17 wherein the means for monitoring the temperature of the support means comprises a temperature sensitive element.
 19. The system of claim 17 wherein the first temperature setpoint control comprises a potentiometer for setting the temperature at which the support means is to be maintained during the reaction. 